Values of T
2 (x, y) and S (TE=0, x, y) were then calculated on a pixel-wise basis, assuming exponential decay, i.e., ln(S[x, y, n])=ln(S[TE=0], x, y)–TE (n)/T
2(x, y), where (x, y) describes the location of the pixel, n characterizes the echo number, from 1 to 32, and S is the image signal intensity. Linear least-squares regression was used to calculate a single T
2 relaxation time measure for each pixel (x, y). Calculations of regional T
2 relaxation time were made for regions of interest drawn manually under the guidance of conventional T
1-weighted matched MRI images of two to four slices through the cerebellum by using anatomic boundaries observed in T
1-weighted, preliminary T
2 relaxometry maps and an atlas of the cerebellum
+(31). Region-of-interest slice selections were based on an assessment of the presence of CSF in order to minimize partial volume artifacts, which result in abnormally elevated T
2 relaxation times (values >100 msec were rejected). Sixteen voxel regions of interest in the vermis were conservatively limited to square regions (x=6 mm by y=6 mm) to avoid encroaching into ventricular space and to provide consistency between slices and subjects. Representative cerebellar regions of interest are depicted in
+Figure 1. Delineation of regions and analysis of imaging data were performed on coded images by an analyst who was familiar with cerebellar anatomy and was blind to the identity, diagnosis, and treatment conditions of the subject. The coefficient for intrarater reliability, alpha, was 0.987, based on four separate and independent T
2 relaxation time measures from the vermis of seven subjects. Regional T
2 relaxation times were calculated from the median value of all the designated pixels, as the median provides a regional estimate that is less susceptible to contamination by spurious values from CSF than does the mean. Regional T
2 relaxation time values were averaged for all slices within subjects, and differences between placebo and drug conditions were then calculated.